KR100393137B1 - Forming Method of the porous layer on the surface at the Implant - Google Patents
Forming Method of the porous layer on the surface at the Implant Download PDFInfo
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- KR100393137B1 KR100393137B1 KR10-2001-0008669A KR20010008669A KR100393137B1 KR 100393137 B1 KR100393137 B1 KR 100393137B1 KR 20010008669 A KR20010008669 A KR 20010008669A KR 100393137 B1 KR100393137 B1 KR 100393137B1
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- 239000007943 implant Substances 0.000 title claims abstract description 42
- 238000000034 method Methods 0.000 title claims abstract description 28
- 239000011324 bead Substances 0.000 claims abstract description 29
- 239000011230 binding agent Substances 0.000 claims abstract description 22
- RTAQQCXQSZGOHL-UHFFFAOYSA-N Titanium Chemical compound [Ti] RTAQQCXQSZGOHL-UHFFFAOYSA-N 0.000 claims abstract description 21
- 239000010936 titanium Substances 0.000 claims abstract description 21
- 229910052719 titanium Inorganic materials 0.000 claims abstract description 20
- 238000005245 sintering Methods 0.000 claims abstract description 14
- 239000011247 coating layer Substances 0.000 claims abstract description 13
- 229910001069 Ti alloy Inorganic materials 0.000 claims abstract description 12
- 239000010410 layer Substances 0.000 claims abstract description 9
- 239000002210 silicon-based material Substances 0.000 claims abstract description 5
- 229910052710 silicon Inorganic materials 0.000 abstract description 7
- XUIMIQQOPSSXEZ-UHFFFAOYSA-N Silicon Chemical compound [Si] XUIMIQQOPSSXEZ-UHFFFAOYSA-N 0.000 abstract description 6
- 239000010703 silicon Substances 0.000 abstract description 6
- 230000012010 growth Effects 0.000 abstract description 3
- 230000001737 promoting effect Effects 0.000 abstract description 2
- 238000010586 diagram Methods 0.000 description 5
- 210000002449 bone cell Anatomy 0.000 description 4
- 239000000843 powder Substances 0.000 description 4
- 108010010803 Gelatin Proteins 0.000 description 3
- 229910052799 carbon Inorganic materials 0.000 description 3
- 229920000159 gelatin Polymers 0.000 description 3
- 239000008273 gelatin Substances 0.000 description 3
- 235000019322 gelatine Nutrition 0.000 description 3
- 235000011852 gelatine desserts Nutrition 0.000 description 3
- 239000000463 material Substances 0.000 description 3
- 239000000203 mixture Substances 0.000 description 3
- 239000003039 volatile agent Substances 0.000 description 3
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 2
- 229910045601 alloy Inorganic materials 0.000 description 2
- 239000000956 alloy Substances 0.000 description 2
- 238000005275 alloying Methods 0.000 description 2
- 210000000988 bone and bone Anatomy 0.000 description 2
- 238000005260 corrosion Methods 0.000 description 2
- 230000007797 corrosion Effects 0.000 description 2
- 238000004519 manufacturing process Methods 0.000 description 2
- 229910052751 metal Inorganic materials 0.000 description 2
- 239000002184 metal Substances 0.000 description 2
- 239000011148 porous material Substances 0.000 description 2
- 150000003377 silicon compounds Chemical class 0.000 description 2
- 230000010261 cell growth Effects 0.000 description 1
- 150000001875 compounds Chemical class 0.000 description 1
- 238000011109 contamination Methods 0.000 description 1
- 238000009792 diffusion process Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 210000003414 extremity Anatomy 0.000 description 1
- 239000000835 fiber Substances 0.000 description 1
- 239000004519 grease Substances 0.000 description 1
- 210000004394 hip joint Anatomy 0.000 description 1
- 229910052739 hydrogen Inorganic materials 0.000 description 1
- 238000002513 implantation Methods 0.000 description 1
- 229910052760 oxygen Inorganic materials 0.000 description 1
- 230000000704 physical effect Effects 0.000 description 1
- 229920001296 polysiloxane Polymers 0.000 description 1
- 230000001172 regenerating effect Effects 0.000 description 1
- 150000003609 titanium compounds Chemical class 0.000 description 1
Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2/30907—Nets or sleeves applied to surface of prostheses or in cement
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/02—Inorganic materials
- A61L27/04—Metals or alloys
- A61L27/06—Titanium or titanium alloys
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F7/00—Manufacture of composite layers, workpieces, or articles, comprising metallic powder, by sintering the powder, with or without compacting wherein at least one part is obtained by sintering or compression
- B22F7/002—Manufacture of composite layers, workpieces, or articles, comprising metallic powder, by sintering the powder, with or without compacting wherein at least one part is obtained by sintering or compression of porous nature
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J9/00—Working-up of macromolecular substances to porous or cellular articles or materials; After-treatment thereof
- C08J9/0014—Use of organic additives
- C08J9/0042—Use of organic additives containing silicon
-
- C—CHEMISTRY; METALLURGY
- C23—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; CHEMICAL SURFACE TREATMENT; DIFFUSION TREATMENT OF METALLIC MATERIAL; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL; INHIBITING CORROSION OF METALLIC MATERIAL OR INCRUSTATION IN GENERAL
- C23C—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; SURFACE TREATMENT OF METALLIC MATERIAL BY DIFFUSION INTO THE SURFACE, BY CHEMICAL CONVERSION OR SUBSTITUTION; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL
- C23C24/00—Coating starting from inorganic powder
- C23C24/08—Coating starting from inorganic powder by application of heat or pressure and heat
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00023—Titanium or titanium-based alloys, e.g. Ti-Ni alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00395—Coating or prosthesis-covering structure made of metals or of alloys
- A61F2310/00407—Coating made of titanium or of Ti-based alloys
Landscapes
- Chemical & Material Sciences (AREA)
- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Materials Engineering (AREA)
- Medicinal Chemistry (AREA)
- Transplantation (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Organic Chemistry (AREA)
- Chemical Kinetics & Catalysis (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Mechanical Engineering (AREA)
- Heart & Thoracic Surgery (AREA)
- Vascular Medicine (AREA)
- Biomedical Technology (AREA)
- Polymers & Plastics (AREA)
- Cardiology (AREA)
- Inorganic Chemistry (AREA)
- Dermatology (AREA)
- Epidemiology (AREA)
- Composite Materials (AREA)
- Manufacturing & Machinery (AREA)
- Orthopedic Medicine & Surgery (AREA)
- Metallurgy (AREA)
- Materials For Medical Uses (AREA)
- Prostheses (AREA)
Abstract
본 발명은 티타늄을 주성분으로 형성된 임플란트 표면에 다공질층을 형성시키는 방법에 관한 것으로, 임플란트 표면에 티타늄 또는 티타늄 합금 비드(21)를 규소계 화합물을 바인더(22)로 하여 혼합한 후 도포하여 비드 코팅층을 성형하는 단계와, 비드 코팅층이 성형된 임플란트(10)를 진공하에서 예비 소결하여 바인더 내의 휘발성분을 휘발 제거 한후 소결과정에서 규소를 티타늄 또는 티타늄 합금 내로 확산시켜 티타늄과 규소의 공정과정에 의해 목성장(Neck growth)이 촉진되어 임플란트(10) 표면에 3차원의 서로 연결된 다공질(30)코팅층을 형성시키는 방법에 관한 것이다.The present invention relates to a method for forming a porous layer on the surface of the implant formed mainly of titanium, titanium or titanium alloy beads (21) on the surface of the implant mixed with a silicon-based compound as a binder 22 and then applied to the bead coating layer And sintering the implant 10 in which the bead coating layer was formed under vacuum to remove volatilized components in the binder, and then diffusing silicon into titanium or a titanium alloy during the sintering process. The invention relates to a method of promoting growth of the neck to form a porous 30 coating layer connected to each other on the surface of the implant 10 in three dimensions.
Description
본 발명은 임플란트 표면의 다공질층 형성방법에 관한 것으로, 상세하게는 고강도와 더불어 내식성, 생체 적합성이 우수한 티타늄으로 형성된 임플란트의 표면에 뼈 세포의 성장을 촉진시켜 초기 안정성을 향상시키기 위한 목적으로, 금속 비드 또는 금속섬유를 소결시키거나 확산 접합시켜 표면에 다공질층을 형성시켜 주는 방법에 관한 것이다.The present invention relates to a method for forming a porous layer on the surface of an implant, and more particularly, to promote bone cell growth on the surface of an implant formed of titanium having high strength, corrosion resistance and biocompatibility, and to improve initial stability. A method for forming a porous layer on a surface by sintering or diffusion bonding beads or metal fibers.
일반적으로 임플란트느 인공고광절 또는 인공치아로써 사용되는데, 인체 내에 삽입 시술되는 관계로 특수한 성질이 요구된다. 즉, 생체적합성이 우수하여야 하며, 내식성 및 높은 강도가 요구된다.In general, implants are used as artificial high extremities or artificial teeth, which require special properties as they are inserted into the human body. That is, the biocompatibility must be excellent, corrosion resistance and high strength are required.
이러한 특수한 성질이 요구되는 이유는, 인체 내에 삽입되어 일정기간 손상되지 않고 뼈와 같은 강도를 유지하지 못하는 경우, 이에 따른 재 시술이 필요하게 되어 여러번의 시술에 따른 어려움을 방지하기 위함이다.The reason why such a special property is required is that when inserted into the human body is not damaged for a certain period of time and does not maintain the bone-like strength, re-treatment is required accordingly to prevent the difficulty of the multiple procedures.
특히, 인체 내의 뼈는 재생력을 보유하고 있어 인체내에 장기간 삽입된 임플란트 표면에는 뼈 세포가 성장하게 되고, 뼈 세포의 성장에 의해 임플란트는 원래 인체의 뼈와 일체로 결합되는 효과를 볼 수 있다.In particular, the bone in the human body has regenerative power so that bone cells grow on the surface of the implant inserted into the human body for a long time, and by implantation of the bone cells, the implant can be combined with the original human bone.
이러한 이유로 임플란트는 생체 적합성이 우수한 재질이 사용되며, 뼈 세포의 성장을 촉진하기 위한 목적으로 그 표면에 다공질층을 형성시키고 있다. 따라서 상술한 성질을 갖는 금속인 티타늄이 임플란트용으로 사용되고 있다.For this reason, the implant is made of a material having excellent biocompatibility, and forms a porous layer on its surface for the purpose of promoting the growth of bone cells. Therefore, titanium, which is a metal having the above-described properties, is used for implants.
종래 임플란트 표면에 다공질층을 형성하는 방법은, 티타늄으로 형성된 임플란트 표면에 순수 티타늄이나 티타늄 합금의 비드를 젤라틴(gelatin)을 바인더로 하여 혼합한 후, 임플란트 표면에 도포하여 비드 코팅층을 성형하는 단계와, 비드 코팅층이 형성된 임플란트를 고온, 진공하에서 소결하는 단계로 구성되어 있다. 그 러나, 상술한 방법은 젤라딘을 바인더로 사용할 때, 젤라틴에 잔존하는 카본과 티타늄과의 공정온도가 1648℃로 비교적 높기 때문에 티타늄 또는 티타늄 합금 비드에 있어서 공정온도를 낮추는 효과는 기대할 수 없어 고온에서 소결하여야 하는 문제가 있고, 이러한 문제를 해결하기 위한 수단으로 다른 합금원소 분말을 첨가하여 공정온도를 낮추는 방안이 있으나, 이 경우에도 추가로 작업을 하여야 하며 합금원소 분말 첨가시 티타늄 또는 티타늄 합금 비드의 오염이 발생되는 문제가 있었다.Conventionally, a method of forming a porous layer on the surface of an implant includes mixing beads of pure titanium or a titanium alloy with gelatin as a binder on an implant surface formed of titanium, and then applying the surface to the implant to form a bead coating layer; It is composed of a step of sintering the implant formed with a bead coating layer under high temperature, vacuum. However, in the above-mentioned method, when using gelatin as a binder, the process temperature of carbon and titanium remaining in the gelatin is relatively high at 1648 ° C., so the effect of lowering the process temperature in titanium or titanium alloy beads cannot be expected. There is a problem to be sintered at, and there is a way to reduce the process temperature by adding other alloying element powder as a means to solve this problem, but in this case, additional work must be done, and titanium or titanium alloy beads when alloying element powder is added There was a problem of contamination.
따라서, 본 발명이 이루고자 하는 기술적 과제는 전술한 문제점을 해결할 수 있도록 임플란트와 티타늄 또는 티타늄 합금 비드의 바인더를, 카본이 소량 함유되며 결합력을 갖는 물질로 대체하여 티타늄과의 공정온도를 낮추어 주는 바인더를 사용하는 방법을 제공함에 있다.Therefore, the technical problem to be achieved by the present invention is to replace the binder and the binder of the implant and titanium or titanium alloy beads with a small amount of carbon and a binder material to reduce the process temperature with titanium to solve the above problems To provide a method of use.
도 1은 본 발명의 개략 공정도,1 is a schematic process diagram of the present invention;
도 2는 임플란트 표면에 도포된 비드-바인더의 혼합물을 도시한 개략도,2 is a schematic view showing a mixture of bead-binders applied to an implant surface,
도 3은 임플란트를 소결한 후 접합된 비드를 도시한 개략도,3 is a schematic diagram showing beads bonded after sintering an implant,
도 4는 임플란트를 소결한 후 접합된 비드형태의 사진.Figure 4 is a photograph of a bead form bonded after sintering the implant.
〔도면중 주요부호에 관한 설명〕[Description of Major Code in Drawing]
10 ... 임플란트 20 ... 혼합물10 ... Implants 20 ... Mixtures
21 ... 비드 22 ... 바인더21 ... Bead 22 ... Binder
30 ... 기공30 ... pore
상술한 기술적 과제를 달성하기 위하여 본 발명에서는 티타늄과 낮은 온도(1330℃)에서 공정을 형성하며 결합력을 갖는 규소계 화합물을 바인더로 사용한다.In order to achieve the above technical problem, the present invention uses a silicon-based compound having a bonding force and forming a process at a low temperature (1330 ° C.) with titanium.
본 발명은 임플란트 표면에 티타늄 또는 티타늄 합금 비드를 규소계 화합물을 바인더로 하여 혼합하고 도포하여 비드 코팅층을 성형하는 단계와, 비드 코팅층이 성형된 임플란트를 고온 진공상태에서 소결하는 단계로 구성된다.The present invention consists of forming a bead coating layer by mixing and applying titanium or titanium alloy beads with a silicon-based compound as a binder on the implant surface, and sintering the implant formed with the bead coating layer in a high temperature vacuum state.
이하 본 발명의 일 실시예를 첨부된 도면으로 설명한다.Hereinafter, an embodiment of the present invention will be described with the accompanying drawings.
도 1은 본 발명을 도시한 개략공정도이고, 도 2는 임플란트 표면에 도포된 비드-바인더의 혼합물을 도시한 개략도이며, 도 3은 임플란트를 소결한 후 접합된 비드를 도시한 개략도이고, 도 4는 임플란트를 소결한 후 접합된 비드형태의 사진이다.Figure 1 is a schematic process diagram illustrating the present invention, Figure 2 is a schematic diagram showing a mixture of bead-binder applied to the implant surface, Figure 3 is a schematic diagram showing beads bonded after sintering the implant, Figure 4 Is a bead-shaped photograph bonded after sintering the implant.
(실시예)(Example)
100∼300㎛의 크기를 가지는 티타늄 또는 티타늄 합금 비드(21)를 준비하고, 바인더(22)로서 Si, O, C, H를 주요 구성물질로 하는 Dow Corning사의 실리콘 화합물을 이용하여 서로 혼합하였다.Titanium or titanium alloy beads 21 having a size of 100 to 300 µm were prepared and mixed with each other using Dow Corning's silicon compound whose main components were Si, O, C, and H as binder 22.
바인더로 사용된 물질은 실리콘 화합물로서, 물리적 특성은 점성이 강하고 윤활성이 좋은 Grease이며, 비드와 바인더의 비율은 질량비 1:10으로 하였다. 혼합된 바인더(22)와 비드(21)를 상온에서 임플란트(10) 표면에 도포하여 비드(21)와 비드(21), 비드(21)와 임플란트(10)를 도 2와 같이 결합시킨 후, 1×10-3torr의 진공상태에서 400℃를 유지하며 4시간 에비소결을 실시하였다.The material used as the binder was a silicone compound, and the physical properties were grease with high viscosity and good lubricity, and the ratio of beads and binder was 1:10 by mass. After the mixed binder 22 and the beads 21 are applied to the surface of the implant 10 at room temperature to combine the beads 21 and beads 21, the beads 21 and the implant 10 as shown in FIG. The sintering was carried out for 4 hours at 400 ° C. in a vacuum of 1 × 10 −3 torr.
온도의 승온속도는 20℃/분으로 하였으며, 승온 중에 700℃에서 1시간 동안 유지하여 바인더 내의 잔여 휘발성 물질을 제거하였다.The temperature increase rate was 20 ° C / min, and maintained at 700 ° C for 1 hour during the temperature increase to remove residual volatiles in the binder.
예비소결이 완료된 임플란트(10)를 1×10-5torr의 진공상태에서 1200∼1300℃ 온도범위를 유지하여 2∼4시간 동안 소결하였다.The pre-sintered implant 10 was sintered for 2 to 4 hours while maintaining a temperature range of 1200 to 1300 ° C. in a vacuum state of 1 × 10 −5 torr.
소결이 완료된 후, 임플란트를 상온에서 냉각하고, 전자현미경을 이용하여 촬영한 결과 도 4와 같은 사진을 얻었다.After the sintering was completed, the implant was cooled at room temperature and photographed using an electron microscope to obtain a photo as shown in FIG.
도 4에서 알 수 있듯이, 임플란트의 표면에는 3차원적으로 서로 연결된 기공(30)이 형성된 다공질의 코팅층이 형성됨을 알 수 있다(도 3 참조).As can be seen in FIG. 4, it can be seen that a porous coating layer having pores 30 connected to each other in three dimensions is formed on the surface of the implant (see FIG. 3).
전술한 실시예에서 알 수 있듯이, 본 발명은 티타늄으로 형성된 인공고관절 또는 인공치아와 같은 임플란트(10) 표면에 타티늄 또는 티타늄 합금 비드(21)를규소계 화합물을 바인더(22)로 하여 혼합 도포하여 비드 코팅층을 형성하고, 비드 코팅층이 형성된 임플란트를 1×10-3torr 진공상태에서 400℃로 예비소결을 실시하고, 700℃에서 1시간 유지하여 휘발성 물질을 제거한다.As can be seen in the above-described embodiment, the present invention is mixed by applying a titanium compound or titanium alloy beads 21 as a binder 22 on the surface of the implant 10, such as artificial hip joint or artificial tooth formed of titanium The bead coating layer is formed, and the implant on which the bead coating layer is formed is pre-sintered at 400 ° C. under vacuum at 1 × 10 −3 torr, and maintained at 700 ° C. for 1 hour to remove volatiles.
휘발성 물질이 제거된 임플란트를 1×10-5torr 진공상태에서 1200∼1300℃에서 2∼4시간 동안 소결시키는데, 소결중 휘발성이 없는 규소는 티타늄 또는 티타늄 합금내로 확산하여 티타늄과 규소의 공정과정에 의해 목성장(Neck growth)이 촉진되어 임플란트 표면에 3차원의 서로 연결된 다공질(30) 코팅층을 형성시켜 주게되는 것이다.Implants from which volatiles have been removed are sintered for 2 to 4 hours at 1200 to 1300 ° C. under vacuum at 1 × 10 -5 torr. During the sintering, the non-volatile silicon diffuses into titanium or titanium alloys to process titanium and silicon. Neck growth is thereby promoted to form three-dimensional porous 30 coating layers connected to each other on the implant surface.
즉, 본 발명의 특징은 바인더로 규소계 화합물을 사용하여 공정온도를 낮추어 주며, 공정 형성원소인 규소가 바인더 자체에 함유되어 있어 부가적인 다른 합금원소 분말의 첨가가 생략될 수 있다.That is, a feature of the present invention is to lower the process temperature by using a silicon-based compound as a binder, and silicon, which is a process forming element, is contained in the binder itself, so that the addition of additional alloy powder may be omitted.
본 발명에 따르면, 바인더로 규소 화합물을 사용함으로써, 티타늄과 규소의 공정온도(1330℃)에서 공정시킴으로 상대적으로 낮은 온도에서 작업이 가능하며, 바인더 자체에 공정 형성원소인 규소가 함유되어 부가적인 합금원소 분말의 첨가작업을 생략할 수 있어 제조공정의 단순화와 제조원가를 절감하는 효과가 있다.According to the present invention, by using a silicon compound as a binder, it is possible to work at a relatively low temperature by processing at a process temperature (1330 ℃) of titanium and silicon, and the binder itself contains silicon as a process forming element additional alloy The addition of the elemental powder can be omitted, thereby simplifying the manufacturing process and reducing the manufacturing cost.
Claims (3)
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| KR10-2001-0008669A KR100393137B1 (en) | 2001-02-21 | 2001-02-21 | Forming Method of the porous layer on the surface at the Implant |
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| KR10-2001-0008669A KR100393137B1 (en) | 2001-02-21 | 2001-02-21 | Forming Method of the porous layer on the surface at the Implant |
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Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH02286155A (en) * | 1989-04-27 | 1990-11-26 | Ishikawajima Harima Heavy Ind Co Ltd | artificial tooth root |
| JPH0531168A (en) * | 1991-07-30 | 1993-02-09 | Isuzu Motors Ltd | Production of implant material for living body |
| US5443510A (en) * | 1993-04-06 | 1995-08-22 | Zimmer, Inc. | Porous coated implant and method of making same |
| JPH07255833A (en) * | 1994-03-24 | 1995-10-09 | Nippon Electric Glass Co Ltd | Organism implant material and manufacture thereof |
| US5773099A (en) * | 1994-01-27 | 1998-06-30 | Injex Corporation | Dental care material and manufacturing method |
| KR20020032959A (en) * | 2000-10-28 | 2002-05-04 | 김성곤 | Porous implant and the same making |
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2001
- 2001-02-21 KR KR10-2001-0008669A patent/KR100393137B1/en not_active Expired - Fee Related
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH02286155A (en) * | 1989-04-27 | 1990-11-26 | Ishikawajima Harima Heavy Ind Co Ltd | artificial tooth root |
| JPH0531168A (en) * | 1991-07-30 | 1993-02-09 | Isuzu Motors Ltd | Production of implant material for living body |
| US5443510A (en) * | 1993-04-06 | 1995-08-22 | Zimmer, Inc. | Porous coated implant and method of making same |
| US5773099A (en) * | 1994-01-27 | 1998-06-30 | Injex Corporation | Dental care material and manufacturing method |
| JPH07255833A (en) * | 1994-03-24 | 1995-10-09 | Nippon Electric Glass Co Ltd | Organism implant material and manufacture thereof |
| KR20020032959A (en) * | 2000-10-28 | 2002-05-04 | 김성곤 | Porous implant and the same making |
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